Catheter imaging probe and method

ABSTRACT

A catheter imaging probe for a patient. The probe includes a conduit through with energy is transmitted. The probe includes a first portion through which the conduit extends. The probe includes a second portion which rotates relative to the conduit to redirect the energy from the conduit. A method for imaging a patient. The method includes the steps of inserting a catheter into the patient. There is the step of rotating a second portion of the catheter relative to a conduit extending through a first portion of the catheter, which redirects the energy transmitted through the conduit to the patient and receives the energy reflected back to the second portion from the patient and redirects the reflected energy to the conduit.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.12/638,927, filed Dec. 15, 2009, now U.S. Pat. No. 8,996,099 which willissue on Mar. 31, 2015; which is a continuation from U.S. applicationSer. No. 10/548,982, filed May 2, 2006, now U.S. Pat. No. 7,711,413issued May 4, 2010; which is a National Phase application of PCTApplication No. PCT/US2004/012773, filed Apr. 23, 2004; which claimspriority to U.S. Provisional Application Ser. No. 60/466,215, filed Apr.28, 2003, all herein incorporated by reference.

BACKGROUND OF THE INVENTION

The present invention relates to optical coherence tomography based onthe use of an optical fiber that does not rotate. More specifically, thepresent invention relates to optical coherence tomography based on theuse of an optical fiber that does not rotate that is enclosed in acatheter that has a tip which does rotate to redirect light from thefiber to a surrounding vessel and the light reflected from the vesselback to the optical fiber.

Myocardial infarction or heart attack remains the leading cause of deathin our society. Unfortunately, most of us can identify a family memberor close friend that has suffered from a myocardial infarction. Untilrecently many investigators believed that coronary arteries criticallyblocked with atherosclerotic plaque that subsequently progressed tototal occlusion was the primary mechanism for myocardial infarction.Recent evidence from many investigational studies, however, clearlyindicates that most infarctions are due to sudden rupture ofnon-critically stenosed coronary arteries due to sudden plaque rupture.For example, Little and coworkers (Little, W C, Downes, T R, Applegate,R J. “The underlying coronary lesion in myocardial infarction:implications for coronary angiography”. Clin Cardiol 1991; 14: 868-874,incorporated by reference herein) observed that approximately 70% ofpatients suffering from an acute plaque rupture were initiated onplaques that were less than 50% occluded as revealed by previouscoronary angiography. This and similar observations have been confirmedby other investigators (Nissen, S. Coronary angiography andintravascular ultrasound. Am J Cardiol 2001; 87 (suppl): 15 A-20 A,incorporated by reference herein).

The development of technologies to identify these unstable plaques holdsthe potential to decrease substantially the incidence of acute coronarysyndromes that often lead to premature death. Unfortunately, no methodsare currently available to the cardiologist that may be applied tospecify which coronary plaques are vulnerable and thus prone to rupture.Although treadmill testing has been used for decades to identifypatients at greater cardiovascular risk, this approach does not have thespecificity to differentiate between stable and vulnerable plaques thatare prone to rupture and frequently result in myocardial infarction.Inasmuch as a great deal of information exists regarding the pathologyof unstable plaques (determined at autopsy) technologies based uponidentifying the well described pathologic appearance of the vulnerableplaque offers a promising long term strategy to solve this problem.

The unstable plaque was first identified and characterized bypathologists in the early 1980's. Davis and coworkers noted that withthe reconstruction of serial histological sections in patients withacute myocardial infarctions associated with death, a rupture orfissuring of atheromatous plaque was evident (Davis M J, Thomas A C.Plaque fissuring: the cause of acute myocardial infarction, suddendeath, and crescendo angina. Br Heart J 1985; 53: 363-373, incorporatedby reference herein). Ulcerated plaques were further characterized ashaving a thin fibrous cap, increased macrophages with decreased smoothmuscle cells and an increased lipid core when compared to non-ulceratedatherosclerotic plaques in human aortas (Davis M J, Richardson P D,Woolf N, Katz D R, Mann J. Risk of thrombosis in human atheroscleroticplaques: role of extracellular lipid, macrophage, and smooth muscle cellcontent, incorporated by reference herein). Furthermore, no correlationin size of lipid pool and percent stenosis was observed when imaging bycoronary angiography. In fact, most cardiologists agree that unstableplaques progress to more stenotic yet stable plaques through progressionvia rupture with the formation of a mural thrombus and plaqueremodeling, but without complete luminal occlusion (Topol E J, RabbaicR. Strategies to achieve coronary arterial plaque stabilization.Cardiovasc Res 1999; 41: 402-417, incorporated by reference herein).Neo-vascularization with intra-plaque hemorrhage may also play a role inthis progression from small lesions (<50% occluded) to largersignificant plaques. Yet, if the unique features of unstable plaquecould be recognized by the cardiologist and then stabilized, a dramaticdecrease may be realized in both acute myocardial infarction andunstable angina syndromes, and in the sudden progression of coronaryartery disease.

In Optical Coherence Tomography (OCT), light from a broad band lightsource is split by an optical fiber splitter with one fiber directinglight to the vessel wall and the other fiber directing light to a movingreference mirror. The distal end of the optical fiber is interfaced witha catheter for interrogation of the coronary artery during a heartcatheterization procedure. The reflected light from the plaque isrecombined with the signal from the reference mirror forminginterference fringes (measured by a photovoltaic detector) allowingprecise depth-resolved imaging of the plaque on a micron scale.

OCT uses a superluminescent diode source emitting a 1300 nm wave length,with a 50 nm band width (distribution of wave length) to make in situtomographic images with axial resolution of 10-20 tm and tissuepenetration of 2-3 mm. OCT has the potential to image tissues at thelevel of a single cell. In fact, the inventors have recently utilizedbroader band width optical sources such as femto-second pulsed lasers,so that axial resolution is improved to 4 μm or less. With suchresolution, OCT can be applied to visualize intimal caps, theirthickness, and details of structure including fissures, the size andextent of the underlying lipid pool and the presence of inflammatorycells. Moreover, near infrared light sources used in OCT instrumentationcan penetrate into heavily calcified tissue regions characteristic ofadvanced coronary artery disease. With cellular resolution, applicationof OCT may be used to identify other details of the vulnerable plaquesuch as infiltration of monocytes and macrophages. In short, applicationof OCT can provide detailed images of a pathologic specimen withoutcutting or disturbing the tissue.

One concern regarding application of this technology to imageatherosclerotic plaques within the arterial lumen is the strongscattering of light due to the presence of red blood cells. Once acatheter system is positioned in a coronary artery, the blood flowbetween the OCT optical fiber and artery can obscure light penetrationinto the vessel wall. One proposed solution is the use of salineflushes. Saline use is limited in duration, however, since myocardialischemia eventually occurs in the distal myocardium. The inventors haveproposed the use of artificial hemoglobin in the place of saline.Artificial hemoglobin is non-particulate and therefore does not scatterlight. Moreover, artificial hemoglobin is about to be approved by theUnited States Food and Drug Administration as a blood substitute and cancarry oxygen necessary to prevent myocardial ischemia. Recently, theinventors demonstrated the viability of using artificial hemoglobin toreduce light scattering by blood in mouse myocardium coronary arteries(Villard J W, Feldman M D, Kim Jeehyun, Milner T E, Freeman G L. Use ofa blood substitute to determine instantaneous murine right ventricularthickening with optical coherence tomography. Circulation 2002; Volume105: Pages 1843-1849, incorporated by reference herein).

The first prototype of an OCT catheter to image coronary plaques hasbeen built and is currently being tested by investigators in Boston atHarvard—MIT (Jang I K, Bouma B E, Kang D H, et al. Visualization ofcoronary atherosclerotic plaques in patients using optical coherencetomography: comparison with intravascular ultrasound. JACC 2002; 39:604-609, incorporated by reference herein) in association with Light LabCo. The prototype catheter consists of a single light source and is ableto image over a 360 degree arc of a coronary arterial lumen by rotatinga shaft that spins the optical fiber. Because the rotating shaft ishoused outside of the body, the spinning rod in the catheter must rotatewith uniform angular velocity so that the light can be focused for equalintervals of time on each angular segment of the coronary artery.Mechanical drag in the rotating shaft can produce significant distortionand artifacts in recorded OCT images of the coronary artery.Unfortunately, because the catheter will always be forced to makeseveral bends between the entry point in the femoral artery to thecoronary artery (e.g., the 180 degree turn around the aortic arch),uneven mechanical drag will result in OCT image artifacts As theapplication of OCT is shifted from imaging gross anatomical structuresof the coronary artery to its capability to image at the level of asingle cell, non-uniform rotation of the single fiber OCT prototype willbecome an increasingly problematic source of distortion and imageartifact.

Essentially, the current endoscope type single channel OCT systemsdeveloped by Light Lab suffer by non-constant rotating speed that formsirregular images of a vessel target. See U.S. Pat. No. 6,134,003,incorporated by reference herein. Their approach of a rotary shaft tospin a single mode fiber is prone to produce artifact. The catheter willalways be forced to make several bends from its entry in the femoralartery, to the 180 degree turn around the aortic arch, to its finaldestination in the coronary artery. All these bends will cause unevenfriction on the rotary shaft, and uneven time distribution of the lighton the entire 360 degree arch of the coronary artery. As the applicationof OCT is shifted from gross anatomical structures of the coronaryartery to its capability to image at the level of a single cell, thennon-uniform rotation of the single fiber OCT will become even a greatersource of greater artifact.

SUMMARY OF THE INVENTION

Depth-resolved light reflection or Optical Coherence Tomography (OCT) isused in embodiments disclosed herein to identify the pathologicalfeatures that have been identified in the vulnerable plaque.

The embodiments disclosed herein overcome the disadvantage of currentsingle mode OCT endoscopes by putting a rotating part at the end of thefiber probe. The rotating part is driven by biocompatible gas or liquidpumped externally. The rotating part is based on a miniature turbine,screw or water wheel, or nanotechnology. The single mode fiber itselfwill not be turned at all, but only a prism reflecting incident light tothe target vessel wall will rotate at constant speed.

The embodiments disclosed herein pertain to a catheter imaging probe fora patient. The probe comprises a conduit through which energy istransmitted. The probe comprises a first portion through which theconduit extends. The probe comprises a second portion which rotatesrelative to the conduit to redirect the energy from the conduit.

The embodiments disclosed herein pertain to a method for imaging apatient. The method comprises the steps of inserting a catheter into thepatient. There is the step of rotating a second portion of the catheterrelative to a conduit extending through a first portion of the catheter,which redirects the energy transmitted through the conduit to thepatient and receives the energy reflected back to the second portionfrom the patient and redirects the reflected energy to the conduit.

BRIEF DESCRIPTION OF THE DRAWINGS

In the accompanying drawings, the preferred embodiment of the inventionand preferred methods of practicing the invention are illustrated inwhich:

FIG. 1 is a schematic representation of the one embodiment.

FIG. 2 is a cross-section of 2-2 of FIG. 1.

FIG. 3 is a cross-section of 3-3 of FIG. 1.

FIG. 4 is a cross-section of 4-4 of FIG. 1.

FIG. 5 is a schematic representation of a capsule.

FIG. 6 is a schematic representation of a side view of a wheel.

FIG. 7 is a schematic representation of an axial view of the wheel.

FIG. 8 is a schematic representation of a side view of the mill.

FIG. 9 is a schematic representation of an axial view of the mill.

FIGS. 10 a and 10 b are schematic representations of a screw embodiment.

FIG. 11 is a schematic representation of an exploded view of a mass flowembodiment.

FIG. 12 is a schematic representation of electric field direction.

FIG. 13 is a schematic representation of an exploded view of anothermass flow embodiment.

FIGS. 14 a and 14 b are schematic representations of an exploded view ofdeformable material as the media.

FIG. 15 is a schematic representation of an exploded view of anotherdeformable material embodiment.

FIGS. 16 a and 16 b are schematic representations of an electrostaticforce embodiment.

FIG. 17 is a schematic representation of a nanorotor-nanostatorembodiment generally.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Referring now to the drawings wherein like reference numerals refer tosimilar or identical parts throughout the several views, and morespecifically to FIG. 1 thereof, there is shown a catheter imaging probe100 for a patient. The probe 100 comprises a conduit 110 through whichenergy or electromagnetic radiation is transmitted. The probe 100comprises a first portion 120 through which the conduit 110 extends. Theprobe 100 comprises a second portion 130 which rotates relative to theconduit 110 to redirect the energy from the conduit 110.

Preferably, the first portion 120 includes an inlet tube 1 through whichfluid flows and wherein the second portion 130 is turned by flowingfluid from the inlet tube 1. The second portion 130 preferably includesa turbine 4 which is turned by the flowing fluid. Preferably, theturbine 4 includes a rotating center shaft 20 through which the conduit110 extends, and spiral shaped inner grooves 22 which extend from thecenter shaft 20 that provide a rotating torque to the center shaft 20when the flowing fluid flows against the grooves 22 that causes thecenter shaft 20 to rotate about the conduit 110.

The second portion 130 preferably has a reflecting material 24 attachedto the center shaft 20 which redirects the energy from the conduit 110.Preferably, the conduit 110 includes an optical fiber 3. The reflectingmaterial 24 preferably includes a prism 8 or a mirror which reflectslight from the conduit 110, the prism 8 rotating with the center shaft20. Preferably, the turbine 4 includes knobs 5 which support the centershaft 20 which allows the shaft to rotate without wobbling. The firstconduit 110 preferably includes at least one outlet tube 2 through whichfluid flows from the second portion 130.

Preferably, the second portion 130 includes a cover transparent to theenergy which encapsulates the cylinder and contacts the first portion120 so no fluid can escape from the second portion 130 except throughthe outlet tube 2. The second portion 130 preferably includes a cylinderattached to the first portion 120 from which the knobs 5 extend and thatdefines a chamber which fluid from the inlet tube 1 flows through. Theturbine 4 is disposed in the chamber. Preferably, the second portion 130includes an energy field reshaping component, such as a lens 11, whichfocuses the energy onto the patient. The lens 11 can be a microlens,grin lens, or optical fiber lens. The probe 100 preferably includes afluid source 26 connected to the inlet tube 1. Preferably, the fluid inthe fluid source 26 is chosen from the group consisting of nitrogen,helium, saline, water, D5W or artificial blood. The first portion 120 issolid except for the conduit 110 and the inlet and outlet tubes 1, 2.

Preferably, the turbine 4 includes a wart 31 which reflects energycoming through a radiation energy guide 30 back to the radiation energyguide 30 (another optical fiber preferably). The wart 31 rotates withthe second portion 130. The energy reflected by the wart 31 indicatescurrent angular position of the second portion 130. The wart 31identifies one angular position (not all the positions) of the rotatingportion when the light hits and gets back from the wart 31. In this way,it is known the shaft 20 rotates one cycle and also the startingposition of the acquired image on the vessel wall. The wart 31 ispreferably a block shape with a flat wall facing the radiation energyguide 30, to reflect the energy back. It is preferably molded into theshaft 10, and the flat wall can have a reflective material, such as amirror placed on it to increase the reflection. The width of the wart issmall compared to the circumference of the shaft 20, so as to identify agiven point, and is high enough to block the energy emitted fromradiation energy guide 30, so it is reflected by the wart 31.

The embodiments disclosed herein pertain to a method for imaging apatient. The method comprises the steps of inserting a catheter into thepatient. There is the step of rotating a second portion 130 of thecatheter relative to a conduit 110 extending through a first portion 120of the catheter, which redirects the energy transmitted through theconduit 110 to the patient and receives the energy reflected back to thesecond portion 130 from the patient and redirects the reflected energyto the conduit 110.

Preferably, the rotating step includes the step of flowing fluid throughan inlet tube 1 to the second portion 130 to turn the second portion130. The following step preferably includes the step of flowing fluidthrough the inlet tube 1 to turn a turbine 4 of the second portion 130.Preferably, the flowing step includes the step of flowing the fluidagainst spiral shaped inner grooves 22 which extend from a rotatingcenter shaft 20 of the turbine 4 to create a rotating torque on thecenter shaft 20 that causes the center shaft 20 to rotate about theconduit 110 that extends through the center shaft 20. The second portion130 preferably has a reflecting material 24 attached to the center shaft20 which redirects the energy from the conduit 110. Preferably, theconduit 110 is an optical fiber 3.

The reflecting material 24 preferably includes a prism 8 or mirror whichreflects light from the conduit 110, and including the step of rotatingthe prism 8 with the center shaft 20 as the center shaft 20 is rotatedby the flowing fluid. Preferably, the rotating step includes the step ofrotating the center shaft 20 that is supported by knobs 5 of a cylinderof the turbine 4 in which the center shaft 20 is disposed. The flowingstep preferably includes the step of flowing the fluid from the inlettube 1 through the chamber of the cylinder. Preferably, the flowing stepincludes the step of removing the fluid flowing from the cylinder of thesecond portion 130 through at least one outlet tube 2 that extendsthrough the first portion 120.

In the operation of the embodiments disclosed herein, FIG. 1 shows thediagram of turbine 4 based catheter type imaging probe 100 which may beconnected to sample arm of single mode fiber 3 OCT. FIGS. 2, 3 and 4 arecross-sectional images of the probe 100 at cross-section (1), (2), (3).At the center of the probe 100, there is a turbine 4 which is connectedto a prism 8. Gas or liquid flows through an outlet tube 2 into theturbine 4 chamber. The turbine 4 is supported by knobs 5 to maintainconstant position during rotation. At the center of the turbine 4, thereis a hole to place an optical fiber 3 that is glued onto a cylinder 9.During the rotation of the turbine 4, the optical fiber 3 will not moveor rotate at all. All of these parts are capsulated by outmosttransparent cover 10. The material for this transparent cover can be anybiocompatible polymers (e.g. plastic Tygon). Probing light will belaunched from the single mode optical fiber 3 through a lens 11 having acurvature to focus the light onto target tissue area. A rotating prism 8connected to the turbine 4 reflects incoming light toward target tissuearea on the vessel wall. The reflected light from the target tissue goesback into the fiber 3 through the prism 8. A standard analysis on thelight is then performed to obtain the image. See U.S. Pat. No.6,134,003, incorporated by reference herein. Gas or liquid gone throughthe turbine 4 exits the probe 100 through an outlet tube 2. Rotationdirection and speed of the second portion are controlled by the pressuredifference between the inlet 1 and outlet 2.

Applying gas or liquid through an inlet tube 1 pressure is induced tothe turbine 4 which rotates; therefore, a prism 8 put on the end of theturbine 4 rotates too. Finally, an imaging system can scan 360 degreearound the inner vessel wall at constant speed.

Preferred Materials

-   -   Gas: Nitrogen, Helium, CO₂ or any gas that can be dissolved into        blood or tissue relatively easily.    -   Fluid: Saline, D5W, or artificial blood (Oxyglobin)    -   Turbine 4: Stainless steel, plastic Tygon or Teflon    -   Cylinder 9: Teflon    -   Cover 10: Plastic Tygon or any biocompatible transparent plastic

Preferred Dimensions

-   -   Outer diameter of transparent cover 10: 1.2 mm    -   Outer diameter of cylinder 9: 0.8 mm    -   Outer diameter of inlet tube 1: 0.2 mm    -   Outer diameter of outlet tube 2: 0.2 mm    -   Outer diameter of fiber 3: 0.1125 mm

Preferred Characteristics

-   -   Target speed: 720 degree/sec    -   Turbine length: 0.5 mm    -   Turbine pitch: 4 pitch/mm    -   Speed of gas flow: 0.5 mm/sec    -   Turbine area: 0.35̂2*pi=0.38 mm²    -   Volume of the inner cylinder for the turbine: 0.38*0.5=0.19 mm³    -   Target flow rate: 0.19 mm³ /sec

The above are all examples. The embodiments disclosed herein are notlimited to these values. For instance, to obtain a finer image, the flowrate is lower and the time it takes to obtain an image is then longer.

In an alternative preferred embodiment shown in FIGS. 5-9, the secondportion 130 includes a mill 50. The mill 50 preferably includes a wheel52. Preferably, the mill 50 includes a capsule 54 which holds the wheel52. The conduit 54 is preferably an optical fiber 3. Preferably, thewheel 52 includes a plug 56, and fins 58 which extend radially from theplug 56. The plug 56 has a hole at the center which receives the opticalfiber. The fins 58 are pushed by the fluid causing the plug 56 torotate.

The capsule 54 preferably includes an inlet port 60 and an outlet port62. Preferably, the second portion 130 has a reflecting material 24attached to the plug 56 which redirects the energy from the opticalfiber 3. The reflecting material 24 preferably includes a prism 8 whichreflects light from the optical fiber 3, the prism 8 rotating with theplug 56. Preferably, the capsule 54 includes a first pocket 68 and asecond pocket 70, in which a first end 64 of the plug 56 and a secondend 66 of the plug 56 are respectfully disposed, the first and secondpockets 68, 70 maintaining the plug 56 in position in the capsule 54 asthe plug 56 rotates.

The second portion 130 preferably includes a cover 33 transparent to theenergy which encapsulates the capsule 54 and contacts or attaches to thefirst portion 120 so no fluid can escape from the second portion 130except through the outlet tube 2. The cover 333 can be glued to thefirst portion. Alternatively, the cover 33 can be of a long enoughlength that it extends the length of the first portion and the secondportion. During assembly, after the mill (or for that matter theturbine) is connected to the first portion, and then the mill and thefirst portion are inserted into the cover, which is basically a longhollow transparent tube with a closed end. The mill on the end of thefirst portion is then feed through the tube until it is in place at theend of the tube. The flexible tube can be of such an inner diameter thatit forms a tight fit with the outer circumference of the first portionand prevents fluid from escaping the end about the mill except throughthe outlet port.

The probe 100 preferably includes a fluid source 26 connected to theinlet tube 1. Preferably, the fluid in the fluid source 26 is chosenfrom the group consisting of nitrogen, helium, CO₂, saline, water, D5W,ringers lactate or artificial blood.

Preferably, the plug 56 includes a wart 31 which reflects energy comingthrough a radiation energy guide 30 back to the radiation wave guide 30.The wart 31 rotates with the plug 56. The energy reflected by the wart31 indicates current angular position of the second portion 130.

Preferably, the following step includes the step of flowing fluidthrough the inlet tube 1 to turn a wheel 52 of a mill 50 of the secondportion 130. The flowing step preferably includes the step of flowingthe fluid against fins 58 which extend from a rotating plug 56 of thewheel 52 to cause the wheel 52 to rotate about the conduit 54 thatextends through the plug 56. Preferably, the second portion 130 has areflecting material 24 attached to the plug 56 which redirects theenergy from the conduit 54. The conduit 54 preferably is an opticalfiber 3. Preferably, the reflecting material 24 includes a prism 8 whichreflects light from the conduit 54, and including the step of rotatingthe prism 8 with the plug 56 as the wheel 52 is rotated by the flowingfluid. Rotating direction and speed of the second portion are controlledby the pressure difference between the inlet and outlet 60, 62.

The rotating step preferably includes the step of rotating the wheel 52that is disposed in pockets of a capsule 54 of the mill 50 in which thewheel 52 is disposed. Preferably, the flowing step includes the step offlowing the fluid from the inlet tube 1 through an inlet port 60 of thecapsule 54 into the capsule 54. The flowing step preferably includes thestep of removing the fluid flowing from an outlet port 62 of the capsule54 of the second portion 130 through at least one outlet tube 2 thatextends through the first portion 120 so a rotational flow path iscreated with the fluid through the capsule 54 which rotates the wheel 52as the fluid flows against the fins 58.

In the operation of the alternative preferred embodiment, and referringto FIGS. 5-9, the probe 100 is introduced into the patient through thefemoral artery, as is well known in the art, and moved to a desiredlocation in regard to the heart by standard catheterization techniques.Once the probe 100 is at the desired location, a gas, such as nitrogen,CO₂ or helium or any gas that can be dissolved into tissue relativelyeasily or a liquid, such as saline, D5W, lactated ringers or artificialblood (Oxyglobin), is introduced from the fluid source 26 to the inlettube 1 in the first portion 120 of the probe 100. The first portion 120of the probe 100 is essentially solid except for the inlet tube 1, andan outlet tube 2 and the optical fiber 3, which extend through the firstportion 120.

The second portion 130 of the probe 100 is attached, such as by beingglued, to the first portion 120. When the second portion 130 is attachedto the first portion 120, it is aligned properly with the first portion120 so the optical fiber 3 extends from the first portion 120 into thecenter of the second portion 130 along its axis that is hollow toreceive the optical fiber 3. In addition, the inlet tube 1 aligns withan inlet port 60 of the second portion 130, and the outlet tube 2 alignswith the outlet port 62 of the second portion 130 so fluid from theinlet tube 1 flows into the inlet port 60, and fluid from the outletport 62 flows into the outlet tube 2. Both the inlet port 60 and theoutlet port 62 have bends in them to redirect the direction of flow ofthe fluid flowing along the axial direction in the inlet tube 1 towardsa generally radial direction into the second portion 130, and generallyfrom a radially outward direction from the second portion 130 into anaxial direction down the outlet tube 2, respectively. Rotating directionand speed of the second portion are controlled by the pressuredifference between the inlet and outlet 60, 62.

The second portion 130 is in the form of a mill 50 with a wheel 52disposed in a capsule 54. The wheel 52 comprises a plug 56 having ahollow central axis through which the optical fiber 3 extends, and fins58 that extend radially outward from the plug 56. A first end 64 of theplug 56 is disposed in a first pocket 68 of the capsule 54, and a secondend 66 of the plug 56 is disposed in a second end 66 pocket of thecapsule 54. The first and second pockets 68, 70 maintain the plug 56 ina desired location in the capsule 54, while allowing the plug 56 tofreely rotate inside the capsule 54. The plug 56 with the fins 58 isintroduced to the capsule 54 by a cap of the capsule 54 being removed sothe plug 56 can be introduced into the body of the capsule 54. The endof the cap is then fitted back on the body with the first end 64 of theplug 56 disposed in the first pocket 68 and the second end 66 of theplug 56 disposed in the second pocket 70 that is found in the cap.

As fluid flows through the inlet tube 1 to the outlet port 62 and intothe capsule 54, it strikes the fins 58 and causes the fins 58 to moveunder the force of the fluid flow. This movement of the fins 58effectively causes the plug 56 to rotate. The fluid flows against thefins 58 from the inlet port 60 and follows a path about the plug 56 asit rotates and then out the capsule 54 at the outlet port 62 to completeits traverse of the interior of the capsule 54. The fluid leaves theinterior of the capsule 54 through the outlet port 62 and then iscarried away from the capsule 54 through the outlet tube 2 andultimately out of the body of the patient. A rotational fluid path iseffectively created to maintain the plug 56 in rotation by the fluidentering the capsule 54 through the inlet port 60 at a point above theplug 56 relative to the outlet port 62 that is disposed below the plug56. Rotating direction and speed of the second portion are controlled bythe pressure difference between the inlet and outlet 60, 62.

When the plug 56 rotates, a prism 8 disposed at the first end 64 is inalignment with the central axis of the plug 56, and thus the centralaxis of the optical fiber 3, and rotates at the same speed as plug 56.The optical fiber 3, which is disposed in the center of plug 56 isessentially out of contact with plug 56, and stays still as the plug 56rotates about it due to the action of the fluid turning the fins 58. Thelight emitted from the optical fiber 3 is redirected by the prism 8radially outwards towards the interior wall of the vessel in which theprobe 100 is disposed. The rotation of the prism 8 causes the light tobe scanned across a continuous arc, around and around across thecircumference of the interior wall of the vessel. A cover 33 covers thecapsule 54 and protects the capsule 54 from the environment inside thevessel, such as from blood or other fluids or particles. The cover 33 istransparent to allow the light emitted from the optical fiber 3 to passthrough it and strike the vessel, and from light reflected by theinterior of the vessel to pass back through the cover 33 towards theprism 8, where it is once again redirected this time into the opticalfiber 3 from whence it once came. The reflected light, however, nowcarries with it information about the properties of the vessel that havecaused changes in the light and manifested in the reflected light thatis transmitted back along the optical fiber 3 and outside the patient toan analyzer. The analyzer then uses well known techniques to analyze thereflected light that it has received.

The mill 50 and the fins 58 are, for example, made of stainless steel,Mg alloy, plastic, Tygon, or Teflon. The capsule 54 is, for instance,made of Teflon. The cover 33 is, for instance, made of plastic Tygon orany biocompatible transparent plastic. The outer diameter of the probe100 is approximately 1 mm. The approximate tip length of the secondportion 130 of the probe 100 is 5 mm. A target rotating speed for thewheel 52 is about 720 degrees per second, with a target flow rate ofabout 0.19 mm³ per second of fluid flowing through the capsule 54.

As shown in FIGS. 10 a and 10 b, a screw embodiment can also be used,with fluid flow direction moving the screw forward or back depending onthe direction of the fluid flow.

See FIG. 17 for reference to the following descriptions regardingdifferent embodiments of nanotechnology based probe tips.

Mass Flow:

If the media is a solution, a mass flow can be generated in the solutionto provide the torque actuating the rotor, as shown in FIG. 11. Theflow-actuated turbine that is desirable above is one example. In thatcase, the mass flow is the flow of the flowing fluid.

Mass flow could be ions flow. When the media is a kind of electrolyte,such as NaCl solution, an electric field can be provided to make theions, such as Na⁺ and Cl⁻, move toward opposite directions. The massflow generated from the movement of the ions would provide a netmomentum that makes the solvent, that is, the water flow. An electricfield that surrounds the shaft of the nanomotor makes it strong enoughto affect the media electrolyte between the stator and the rotor, thewater in the media electrolyte will flow around the shaft such that atorque will be generated between the stator and the rotor. Furthermore,with obstacle structures, such as fans, on the rotor, the torque will bemore sufficiently used. The circular-oriented electric field can beprovided by interlacing electrodes for positive and negative charge, asshown in FIG. 12, around the media area.

Mass flow induced by osmotic force is another choice, as shown in FIG.13. Osmotic force is generated when there is a density differencebetween any two areas in one solution. The solvent would tend to flowtoward the area of the higher solute density. Some people had invented amethod to use this phenomenon. In their devices, although very similarto the above example about electrolyte case, they used dielectric fluidas the media, and they used strongly charged electrodes to provide freeelectrons moving between electrodes such that the electrons would ionizesome molecules of the dielectric fluid. The molecule ions tended to moveto negatively charged electrode and created the density differencerequired for the generation of the osmotic force. This kind of actuationis also named ion-drag actuator.

Material's Deformation

When the media is a solid material, a torque can be generated betweenthe stator and the rotor by periodically generating the deformation inthe media material. Imagine how some caterpillars move without walkingby foot. They typically bend and stretch their bodies periodically, suchthat they can receive movement by means of frictions between their skinsand the sticks on trees. The nanomotor can work in the same way. Likethe electrolyte example above, a circular-oriented “bend and stretch”structure can be made to generate torque about the shaft. In this case,the media material can be only connected to the rotor, only connected tothe stator, or connected to none of them. An example is shown in FIGS.14 a and 14 b, where FIG. 14 b is a detailed view of the rotor and theelectrode.

The term “periodical” implies vibration. The structure is notnecessarily in the “caterpillar” form, but a disk-shaped material can beused that can be vibrated like a Pizza turning on the cooker'sfingertip. Just like a cell phone ringing in vibration mode, it moves oreven rotates on the table. Generally, periodical deformation (orvibration) and friction can generate movement, and the rotation motionwe need is a special case of the movement.

There are several ways the deformation in the material can be achieved.The first is adjusting temperature to change the atomic latticestructure, named “phase”, of the material. Shape memory alloy (SMA) is agood example. Decades of degree's temperature raise can make a properlydesigned SMA structure generating a big geometrical change.

The second one is thermal expansion or contraction, which is a similarconcept like that of the first one, as shown in FIG. 15. The third, inaddition to heat energy, electric field can be used to contract adielectric media material to generate deformation, such as bending.Finally, electric voltage can be directly applied to the media whenpiezoelectric material is used as the media material. Piezoelectricmaterial can generate high deformation and high force and is widelyapplied in ultrasonic motors, in which an electric wave of highfrequency is used to actuate a piezoelectric structure disposed betweenthe rotor and the stator (In most cases, the rotor itself is thepiezoelectric structure). See FIGS. 16 a and 16 b, where FIG. 16 b is adetailed view of the rotor and the electrodes.

In most cases, the rotor is combined with the media structure. The rotorhas teeth formed around it. For instance, in a triangular shape, whichallows the rotor to slide along the slope of the hypotamous in onedirection but not move back against the vertical edge. The stator isfurther comprised of a plurality of electrodes surrounding the rotorwithout contact. In operation, the electrodes are chargedinterchangably, such to generate induced charge on the teeth of therotor. The attracting force between the teeth and the electrodes thengenerates a torque.

Generally, additional applications for the probe 100 include:

(1) GI tract. Colonoscopy and Endoscopy both currently can only exam thesurface of the GI tract. When suspicious areas that may represent cancerare identified, a biopsy is required. OCT has the advantage ofvisualizing 2-4 mm into the wall of the GI tract and has resolution tothe level of a single cell. The probe can provide histological imageswithout the need to biopsy tissue to visualize and diagnose cancer inreal time.

(2) GU tract. Cystoscopy is a method to visualize the bladder with alight source to aid in the diagnosis of transitional cell cancer of theinner surface of the bladder wall. Application of cystoscopy requires abiopsy to make the final diagnosis of transitional cell cancer. Theprobe 100 can penetrate several millimeters into the bladder wall,visualize at the single cell level, and make a diagnosis of transitionalcell cancer without removing tissue.

(3) Cervical and uterine cancer. Currently the gold standard fordiagnosing cervical cancer is a pap smear, where cells are scraped offthe cervix, and examined under a light microscope to diagnoses cancer.Similarly, women also have the inner lining of the uterus scraped andexamined under a microscope to identify cancer cells. The probe 100 canimage dysplastic and malignant lesions and quantify changes in thenucleous.

Although the invention has been described in detail in the foregoingembodiments for the purpose of illustration, it is to be understood thatsuch detail is solely for that purpose and that variations can be madetherein by those skilled in the art without departing from the spiritand scope of the invention except as it may be described by thefollowing claims.

What is claimed is:
 1. A catheter imaging probe comprising: a conduitthrough which electromagnetic radiation is transmitted; a first portionthrough which the conduit extends; and a second portion which providesmovement relative to the conduit to redirect the electromagneticradiation from the conduit by a movement of mass flow of ions; and anelectric field generates the movement of the mass flow.
 2. A probe asdescribed in claim 1 wherein the first portion includes at least twointerlacing electrodes to generate a positive and a negative charge. 3.A probe as described in claim 2 wherein the second portion includes arotor through which the conduit extends and a transparent covercontaining the rotor, the rotor and inner surface of the capsule definesthe movement of mass flow of ions about the rotor and the first conduitincludes a separator to seal the mass flow of ions in the secondportion, as to generate a circular-oriented electric field causing therotor to rotate about the conduit via reactive force provided by themass flow of ions.
 4. A probe as described in claim 3 wherein the massflow is a dielectric fluid including strongly charged electrodes togenerate molecule ions; and the molecule ions move to the negativecharge electrode to create a density difference of osmotic force.
 5. Aprobe as described in claim 4 wherein the second portion has one or moreoptical redirection elements attached to the center shaft whichredirects the electromagnetic radiation from the conduit.
 6. A probe asdescribed in claim 5 wherein the conduit is a radiation waveguide.
 7. Aprobe as described in claim 6 wherein the radiation waveguide is asingle mode fiber.
 8. A probe as described in claim 7 wherein theoptical redirection element includes a prism which reflects light fromthe conduit, the prism rotating with the center shaft.
 9. A catheterimaging probe comprising: a conduit through which electromagneticradiation is transmitted; a first portion through which the conduitextends; and a second portion which provides movement relative to theconduit to redirect the electromagnetic radiation from the conduit bygenerating the deformation in a media material about the second portion.10. A probe as described in claim 9, wherein the first portion includesan electrode and the second portion includes actuating materials.
 11. Aprobe as described in claim 10, wherein the actuating materials are ashape memory alloy to generate deformation.
 12. A probe as described inclaim 10, wherein the actuating materials are a thermal expansivematerial to generate deformation.
 13. A probe as described in claim 10,wherein the actuating materials are a dielectric media material.
 14. Aprobe as described in claim 10, wherein the actuating materials are apiezoelectric material to generate deformation.
 15. A catheter imagingprobe comprising: a radiation waveguide concentrically disposed througha nanostator, a medium structure, and a nanorotor; wherein a drivingenergy rotates the nanorotor about the radiation waveguide.
 16. A probeas described in claim 15, wherein the driving energy is an electricfield.
 17. A probe as described in claim 16, wherein the nanorotor isoperably coupled to an optical redirection element to receive opticalenergy from the radiation waveguide.